DE102014201944A1 - RF pulse adjustment method and RF pulse adjustment device - Google Patents

Abstract

An HF pulse adjustment method (JV, 300, 400, 500) is used for determining when a magnetic resonance system (1) with a plurality of radio-frequency transmission channels (S1,..., SN) is activated in parallel with the operation RF pulse trains (b1, ..., bN) are transmitted, used Sendeskalierungsfaktoren (SF1, ..., SFN) described. When driving for several of the high-frequency transmission channels (S1, ..., SN), a common Referenzpulszug (bR) is specified. A plurality of candidate images (KB) are taken of an object (O) to be examined with different candidate sets of transmission scaling factors (SF1, ..., SFN). Subsequently, with respect to a given criterion, optimum transmission scaling factors (SF1, ..., SFN) are selected for each of the radio frequency transmission channels (S1, ..., SN) from the recorded candidate images (KB). In addition, a method for controlling a magnetic resonance system (1) using the described HF pulse adjustment method, a correspondingly operating HF pulse adjustment device (19) and a magnetic resonance system (1) with such an HF pulse Adjustment device (19) described.

Description

The present invention relates to an RF pulse adjustment method for determining transmission scaling factors used in the control of a magnetic resonance system with a plurality of radio-frequency transmission channels, via which HF pulse trains are emitted in parallel during operation, wherein in the control for a plurality of the radio-frequency transmission channels common reference pulse train is specified. The invention further relates to an RF pulse adjustment device for a magnetic resonance system, which has a plurality of radio-frequency transmission channels, wherein the RF pulse adjustment device is designed to provide an optimal transmission scaling factor for a plurality of the radio-frequency transmission channels to determine together for the high-frequency transmission channels predetermined Referenzpulszug.

Furthermore, the invention also relates to a method for controlling a magnetic resonance system having a plurality of radio-frequency transmission channels, are transmitted in parallel over the parallel RF pulse trains, wherein for a plurality of radio-frequency transmission channels, a common Referenzpulszug is specified and determines a Sendeskalierungsfaktor for each of the radio-frequency transmission channels is used to calculate the RF pulse trains for the transmit channels based on the reference pulse train.

In addition, the invention relates to a magnetic resonance system having a plurality of radio-frequency transmission channels and a control device which is designed to emit in parallel RF pulse trains for carrying out a desired measurement via the radio-frequency transmission channels.

Finally, the invention relates to a computer program which can be loaded directly into a memory of an HF pulse adjustment device of a magnetic resonance system.

In a magnetic resonance system or magnetic resonance tomography system, the body to be examined is usually exposed with the aid of a basic field magnet system to a relatively high basic field magnetic field (also referred to as "B ₀ field"), for example 3 or 7 Tesla. In addition, a magnetic field gradient is applied by means of a gradient system. High-frequency excitation signals (RF signals) are then emitted via a high-frequency transmission system by means of suitable antenna devices, which is intended to ensure that the nuclear spins of certain resonantly excited atoms determined by this high-frequency field (also referred to as "B ₁ field") are spatially resolved by a defined wavelength Flip angle are tilted relative to the magnetic field lines of the basic magnetic field. This high-frequency excitation or the resulting flip angle distribution is hereinafter also referred to as nuclear magnetization or "magnetization" for short. The relationship between the magnetization m and the B ₁ field irradiated over a time T results according to FIG

Here, the γ gyromagnetic moment, t is the time variable and B ₁ (t) is the time-varying magnetic field strength of the B ₁ field. During the relaxation of the nuclear spins, high-frequency signals, so-called magnetic resonance signals, are emitted, which are received by means of suitable receiving antennas and then further processed. From the thus acquired raw data finally the desired image data can be reconstructed. The transmission of the high-frequency signals to the nuclear spin magnetization is usually carried out by means of a so-called "whole-body coil", also called "body coil", or sometimes with applied to the patient or subject local coils. A typical structure of a whole body coil is a cage antenna (birdcage antenna), which consists of several transmitting rods, which are arranged parallel to the longitudinal axis running around a patient's room of the scanner in which a patient is in the examination. On the front side, the antenna rods are connected to one another in a ring-shaped capacitive manner.

So far it has been common to operate whole body antennas in a "CP mode" (circular polarized mode). For this purpose, a single temporal RF signal is given to all components of the transmitting antenna, for example all transmitting rods of a cage antenna. Usually, the transfer of the pulses with the same amplitude to the individual components is carried out in phase with one of the geometry of the transmitting coil adapted displacement. For example, in a cage antenna with 16 bars, the bars can each be driven offset with the same RF magnitude signal with 22.5 ° phase shift. The result is then one in the x / y plane, i. H. perpendicular to the z-axis extending longitudinal axis of the cage antenna, circularly polarized high frequency field.

gegeben. Dabei ist b_c(t) eine auf dem Kanal c = 1, ..., N auszusendende HF-Kurve, d. h. der Spannungsamplitudenverlauf (in V) eines HF-Pulszugs über der Zeit t, der durch b_c(t) = SF_c·b_R(t) gegeben ist, wobei SF_c der komplexe Skalierungsfaktor für den Kanal c ist und b_R(t) der Spannungsverlauf des Referenzpulszugs. E_c(r) ist die Sensitivität (in μT/V) des Antennenelements des Hochfrequenz-Sendekanals c an einem bestimmten Ort r (d. h. der Pixel- bzw. Voxelposition). Dabei ist E_c(r) die ortsabhängige Sensitivitätsverteilung in Form einer Sensitivitätsmatrix. In the meantime, it is also possible to modify the high-frequency signal to be transmitted, ie the incoming sequence of high-frequency pulses (referred to as "reference pulse train" in the context of the invention) individually in amplitude and phase by a complex transmission scaling factor. The B ₁ field at a location r, ie at a pixel or voxel position r (where r is, for example, a vector with the values of the Cartesian coordinates x, y, z in mm), is in accordance with FIG

given. In this case, b _c (t) is an RF curve to be transmitted on the channel c = 1, ..., N, ie the voltage amplitude curve (in V) of an HF pulse train over time t, which is defined by b _c (t) = SF _c · b _R (t), where SF _{c is} the complex scaling factor for the channel c and b _R (t) is the voltage curve of the reference pulse train. E _c (r) is the sensitivity (in μT / V) of the antenna element of the radio-frequency transmission channel c at a particular location r (ie the pixel or voxel position). E _c (r) is the location-dependent sensitivity distribution in the form of a sensitivity matrix.

Again, the antenna can be operated in the "CP mode" by the amplitude is selected at the same height in all transmission channels and is provided only for a matched to the geometry of the transmitting coil phase shift. In addition, depending on the examination object, a so-called "EP mode" (elliptically polarized mode) is often used, in which the high-frequency field in the x / y plane is not circularly but elliptically polarized. Which mode is used usually depends on the shape of the body region to be stimulated. For objects that are more cylindrically symmetric, for example, when shooting in the head area, the CP mode is more common, with more elliptical shapes, however, such. As in examinations in the chest or abdomen area, rather selected the EP mode. The purpose of the EP mode is to compensate for inhomogeneities of the B ₁ field, which are caused by the non-circularly symmetrical body shape. In many cases, a so-called "B ₁ shimming" of such a multi-channel high-frequency transmission system is performed. Here, the individual Sendeskalierungsfaktoren based on a patient-specific adjustment usually calculated with the aim to achieve a particularly homogeneous excitation compared to the previous standard CP or -EP mode.

To calculate the transmission scaling factors, optimizers are used which minimize the magnitude deviation of the perfectly homogeneous desired target magnetization m from the theoretically achieved actual magnetization A · b: b = arg _b min (|| A · b - m ² ||) (3)

Here, A is the so-called design matrix, consisting of a system of linearly complex equations, in which, among other things, the spatial transmission profiles of the individual transmission channels (antenna rods) and the present B ₀ field distribution are included. This design matrix is z. In W. Grissom et al .: "Spatial Domain Method for the Design of RF Pulses in Multicoil Parallel Excitation", Mag. Res. Med. 56, 620-629, 2006 , described. Here b (t) is the vector of the RF curves b _c (t) to be transmitted in parallel. If the solution of equation (3), ie the minimum of the "objective function" defined in equation (3), is found, the desired scaling factors SF ₁ , SF ₂ ,..., SF _N are present as the result.

To determine the design matrix, appropriate test measurements must first be performed to experimentally determine the coefficients of the design matrix. For this purpose, the patient to be examined must stay in the MRT over the entire duration of the recording and the calculation of the data for the design matrix and the optimal values for the vector of the RF curves and for b (t) and then also the actual examination to endure, which is very stressful especially for sick and weak people. An intermediate exit is not possible for obvious reasons, otherwise due to the inevitable change in position of the patient, the entire adjustment, the B1-shimming, must be repeated.

Thus, there is a problem that due to the necessary adjustment of the B1 field before the actual examination of the patient, the patient must spend too long in the already usually tight arrangement of an MRI device and therefore may feel unwell. This may, for example, lead to a change in position of the patient and thus to a deterioration of the image quality or even to a necessary termination of the image acquisition, if the patient does not hold out until the end of the image acquisition.

It is an object of the present invention to provide an alternative adjustment method as well as a suitable adjustment device, with which a B ₁ -Shimming is possible, in which the duration of the adjustment process can be shortened.

This object is achieved by an HF pulse adjustment method according to claim 1 and by an HF pulse adjustment device according to claim 9.

In the inventive method for adjusting a B ₁ field of a magnetic resonance system, which - as explained above - several, ie at least two, preferably more than two, in principle independently controllable high-frequency transmission channels over which the parallel RF pulse trains are emitted during operation , As usual, a common Referenzpulszug is specified for several of the high-frequency transmission channels, preferably all high-frequency transmission channels. Under such a magnetic resonance systems are in a particularly simple implementation so-called "single-channel systems" to understand, but which are actually a simple form of a two-channel system, the same RF signal (as a common Referenzpulszug) on two channels with an adjustable hardware and / or software devices Phase shift to each other in the antenna is fed (for example, in the CP mode phase-shifted by 90 ° and in the EP mode by 135 ° phase-shifted).

Furthermore, in the RF pulse adjustment method, taking into account a predetermined target magnetization, an individual complex transmission scaling factor is determined for each of the radio frequency transmission channels as a shimming parameter to calculate the RF pulse trains for the transmission channels based on the reference pulse train, e.g. B. as explained above with the Referenzpulszug for the relevant radio-frequency transmission channel to scale or multiply.

According to the invention, however, the transmit scaling factors are now not determined by the abovementioned complex calculation of a linear system of equations in the HF pulse adjustment method, but a series of test images or of candidate images of an object to be examined with different candidate sets of transmission scaling factors is recorded. Subsequently, with respect to a criterion, optimum transmission scaling factors are determined for each of the radio-frequency transmission channels on the basis of the recorded candidate images.

As test images, for example, 2D images or 3D images can be recorded. The object to be examined may be, for example, a patient, in particular a human or an animal or even a mummy or more generally an object that is difficult to access or very sensitive to a direct examination.

The said criterion may be, for example, the homogeneity of the exciting RF field in a target area. It is clear that for all measurements the maximum permissible B1 field and the maximum permissible SAR (applied specific absorption rate) must be observed.

The criterion may also be the achievable mean B1 field (stimulating RF field) within a particular target region that can be maximally achieved with the power provided by the RF amplifier without overloading the RF amplifier.

The criterion may also be the applied specific absorption rate (SAR) needed at a given mean B ₁ value (eg, 11.7 μT) in a particular target region. The criterion can also consist of a combination or a specific weighting of a combination of the stated physical quantities.

In order to determine the physical quantities corresponding to the stated criteria, the following procedure can be selected: The physical quantities corresponding to the individual criteria are determined or calculated on the basis of the image recording or the respective candidate image. A sequence is selected which is sensitive to the local distribution of the stimulating B1 field. This can advantageously be based on a B1-mapping method (or B1-mapping sequences) already described in detail in the literature (see, for example, reference "Chung, Kim, Breton and Axel: Rapid B1 + Mapping Using a Preconditioning RF Pulse with TurboFLASH Readout, Magnetic Resonance in Medicine 64: 439-446 (2010)" and "Nehrke and Börnert: DREAM - A Novel Approach for Robust, Ultrafast, Multislice B1 Mapping, Magnetic Resonance in Medicine 68: 1517-1526 (2012))" , After the acquisition of the candidate images, the B1 distribution is extracted from the respective generated image, wherein the B1 distributions can be determined with the B1 mapping methods referenced above and published. If the homogeneity of the test image or candidate image is determined the calculation of various statistical parameters that are a measure of the homogeneity of the B ₁ field in the chosen region of interest. For example, the quotient is the difference between the maximum value B _1Max and the minimum value B _{1Min of} the magnetic flux density of the B ₁ field and the average value of the magnetic flux density of the B ₁ field B _1Mean to (B _1Max -B _1Min ) / B _1Mean or the standard deviation σ or the arithmetic or geometric mean of the abs error (B ₁ - B _1Mean ).

When determining the maximum mean B ₁ field, the achieved mean B ₁ value in the target region is determined or evaluated. In addition, the maximum RF power of the RF amplifier required for this purpose is determined from the image acquisition parameters. The maximum available power for the current B ₁ shim parameterization is calculated taking into account the HW component protection of the transmission chain (load situation in the antenna). Finally, these values are converted to a maximum mean value of the B ₁ field with full utilization of the available RF power.

When determining the applied specific absorption rate SAR, an evaluation of the mean B ₁ value achieved in the target region is carried out. In addition, an evaluation of the applied SAR from the image acquisition parameters.

Finally, these values are converted to a SAR at a B ₁ reference value (eg 11.7uT).

Accordingly, a suitable RF pulse adjustment device for a magnetic resonance system, which has a plurality of radio-frequency transmission channels, must be designed to use the B ₁ field adjustment method or the RF pulse adjustment method, the transmission scaling factors taking into account a plurality of test images. For this purpose, the HF pulse adjustment device has a candidate image generation unit which is designed to control the magnetic resonance system in such a way that a recording of a plurality of candidate images of an object to be examined is performed with different transmission scaling factors associated with the candidate images. The RF pulse adjustment means comprises a storage unit for storing the captured candidate images and the broadcast scaling factors associated with the respective candidate images, an analysis unit for analyzing the captured candidate images, and a selection unit for selecting optimal broadcast scaling factors with respect to a given criterion based on the analysis of the captured candidate images on.

A magnetic resonance system according to the invention has, in addition to the plurality of radio-frequency transmission channels and the other conventional system components such as a gradient system, a basic field magnet, etc., and a control device which is designed to emit in parallel RF pulse trains for carrying out a desired measurement via the radio-frequency transmission channels. also an inventive RF pulse adjustment device.

In this case, the HF pulse adjustment device can in particular be part of the control device of the magnetic resonance system. In principle, the RF pulse adjustment device but also in an external, z. B. via a network connected to the control device computer, such as an operator terminal or other computer to outsource compute-intensive operations.

Preferably, at least predominant parts of the HF pulse adjustment device are designed in the form of software. The invention thus also encompasses a computer program which can be loaded directly into a memory of an HF pulse adjustment device and / or a control device, with program code sections in order to carry out all steps of the method according to the invention when the program is in the RF pulse -Justage device and / or a control device is executed. Such a software implementation has the advantage that also existing facilities that are used to determine Sendeskalierungsfaktoren or for the B ₁ -Shimming, for example, control devices of existing magnetic resonance systems, by implementing the program can be modified in a suitable manner to in the inventive Way to perform the B ₁ -Shimming.

The dependent claims and the following description contain particularly advantageous developments and refinements of the invention, wherein in particular the claims of one category can be developed analogously to the dependent claims of another claim category. In addition, features of various embodiments can be combined in any way with each other.

In a preferred variant of the method according to the invention, in the HF pulse adjustment method, the recorded candidate images are first analyzed in the determination of the transmission scaling factors and then an optimal candidate image is selected and the optimal transmission scaling factors with respect to a predetermined criterion on the basis of the analyzed candidate images determined information determined.

According to an embodiment of the method that is particularly easy to implement, the transmission scaling factors of the candidate set of transmission scaling factors, which are assigned to the optimum candidate image with respect to a predetermined criterion, are selected as optimal transmission scaling factors.

This is the simplest configuration. Alternatively, using the candidate images and the associated transmit scale factors, the optimal transmit scale factors could eventually be calculated as well.

A particularly simple realization can already take place in the abovementioned "single-channel system", in which e.g. only the CP and EP mode is available, in particular, the phase shift between the pulses on the two channels can also be set via a designed as a hardware switch.

By using such a system, the optimal mode for the current patient can be determined very quickly and easily depending on the recorded candidate images. In this case, only two candidate pictures are taken, one for the CP mode and one for the EP mode. In this embodiment of the method, the selection of the optimal candidate image is based on a candidate image generated with a circularly polarized high frequency magnetic field and a candidate image generated with an elliptically polarized magnetic field.

The candidate images used in the method according to the invention can be, for example, overview images of the object.

The overview images are topograms, also called localizers, which are used in the preparation of the examination of the object in order to define the field of view, also called field of view, for subsequent recording, which serves for "diagnostic" support, for example on a graphical user interface. The overview images can z. B. coronary, sagittal or axial.

The candidate images used for the method according to the invention can show different regions and / or views or sectional planes of the object.

To determine the field of view are always several topograms, z. B. a horizontal longitudinal section through the patient and a vertical longitudinal section and possibly even vertical cross-sections needed. These can now be used according to a particularly advantageous embodiment of the inventive method as provided with different candidate sets of Sendeskalierungsfaktoren test images or candidate images.

Thus, the time and the processing effort can be reduced, which increases the comfort of the patient to be examined and saves costs for the process.

In order to achieve an improved comparability of the candidate images, it may be useful to always use the same area or the same cutting plane for the recording of the candidate images.

According to a particular embodiment of the method, in the analysis of the candidate images, the recorded candidate images are displayed in a display unit and a selection signal is received in a signal receiving unit. The signal receiving unit may be, for example, a user interface.

The selection of the optimal candidate image can also be based on an automatic analysis of the recorded candidate images.

The automatic analysis can be realized on the basis of an image optimization algorithm or evaluation algorithm.

The evaluation algorithm may comprise the following sub-steps: According to the evaluation algorithm, the target values or the physical variables corresponding to the respective predetermined criteria are determined or calculated for each of the acquired scout MR images or candidate images. Depending on the default setting, the B ₁ parameter set or set of transmission scale factors of the candidate image is selected which optimizes a criterion or the weighted superposition of a plurality of criteria or selects those candidate image which most closely corresponds to the given criteria.

In an advanced version, the target criteria and the B ₁ shim parameters are interpolated between the scout images acquired and then a B ₁ shim parameter set or set of transmit scaling factors is selected which is even more optimal.

As already explained above with reference to equation (1), optimization has hitherto generally been carried out in such a way that the target magnetization deviation is minimized in the objective function. In addition, the radiofrequency load (RF load) of the patient can be reduced by a suitable further functional term in the target function. The RF exposure must be limited, as excessive RF exposure could result in patient harm. Therefore, the RF exposure of the patient is usually already calculated in advance in the planning of the high-frequency pulses to be output and the high-frequency pulses are chosen so that a certain limit is not reached. A method for reducing RF exposure is described in 201202092.

As described above, the limitation of the RF load can be realized by means of the RF pulse adjustment method according to the invention by taking into account the maximum B1 field as a criterion in the analysis of the candidate images.

In other words, in the measurement of the candidate images, an evaluation of the required RF power can also be made, i. how the different transmit scaling factors affect RF performance.

The invention will be explained in more detail below with reference to the accompanying figures with reference to embodiments. Show it:

1 a schematic representation of an embodiment of a magnetic resonance system according to the invention,

2 a figure to illustrate a B ₁ -Shimmings,

3 FIG. 3 is a flow chart illustrating the RF pulse adjustment method according to an embodiment of the invention. FIG.

4 FIG. 3 is a flow chart illustrating the RF pulse adjustment method according to a first alternative embodiment of the invention. FIG.

5 a flowchart illustrating the RF pulse adjustment method according to a second alternative embodiment of the invention.

In 1 is roughly schematically a magnetic resonance system according to the invention 1 or a magnetic resonance system 1 shown. It includes the actual magnetic resonance scanner 2 with an examination room in it 8th or patient tunnel 8th , A couch 7 is in this patient tunnel 8th into it, so that a lying on O patient or subject during an examination at a certain position within the magnetic resonance scanner 2 can be stored relative to the magnetic system and high-frequency system arranged therein or can be moved during a measurement between different positions.

Essential components of the magnetic resonance scanner 2 are a basic field magnet 3 , a gradient system 4 with magnetic field gradient coils to apply arbitrary magnetic field gradients in the x, y and z directions, as well as a whole body radio frequency coil 5 , The reception of magnetic resonance signals induced in the examination subject O can take place via the whole-body coil 5 take place, with the usually also the high-frequency signals for inducing the magnetic resonance signals are emitted. Usually, however, these signals are with, for example, placed on or below the object to be examined O local coils 6 receive. All these components are known to those skilled in principle and therefore in the 1 only roughly shown schematically.

The whole body radio frequency coil 5 is here constructed in the form of a so-called birdcage antenna and has a number N of individual antenna rods, which are parallel to the patient tunnel 8th run and around a circumference around the patient tunnel 8th are arranged evenly distributed. At the end, the individual antenna rods are each capacitively connected annularly.

The antenna rods are here as individual transmission channels S ₁ , ..., S _N separately from a control device 10 controllable. It may be a control computer, which may also consist of a plurality of - possibly spatially separated and via suitable cables or the like interconnected - individual computers. Via a terminal interface 17 is this control device 10 with a terminal 20 connected via which an operator the entire system 1 can drive. In the present case this terminal is 20 equipped as a computer with keyboard, one or more screens and other input devices such as a mouse or the like, so that the operator has a graphical user interface available.

The control device 10 includes a gradient control unit 11 on, which in turn can consist of several sub-components. About this gradient control unit 11 The individual gradient coils are connected to control signals SG _x , SG _y , SG _z . These are gradient pulses that are set during a measurement at precisely scheduled time positions and with a precisely predetermined time course.

The control device 10 also has a radio frequency transceiver unit 12 on. This RF transceiver unit 12 also consists of several sub-components, in each case separately and in parallel to the individual transmission channels S ₁ , ... S _N , ie to the individually controllable antenna rods of the whole-body radio-frequency coil 5 To give up high frequency pulses. About the transmitting / receiving unit 12 Magnetic resonance signals can also be received. Usually, however, this happens with the help of the local coils 6 , The with these local coils 6 received signals are received from an RF receiving unit 13 read out and processed. The thereof or the whole-body coil by means of the RF transmitter / receiver unit 12 received magnetic resonance signals are as raw data RD to a reconstruction unit 14 pass, which reconstructs the image data BD and this in a memory 16 deposited and / or via the interface 17 to the terminal 20 so that the operator can look at it. The image data BD can also be stored and / or displayed and evaluated via a network NW at other locations.

The gradient control unit 11 , the radio frequency transceiver unit 12 and the receiving unit 13 for the local coils 6 are each coordinated by a measurement control unit 15 driven. This ensures, by means of appropriate commands, that a desired gradient pulse train GP is emitted by suitable gradient control signals SG _x , SG _y , SG _z , and controls in parallel the RF transceiver unit 12 so that a multi-channel pulse train b is transmitted, ie that on the individual transmission channels S ₁ , ... S _{N in} parallel the appropriate high-frequency pulses to the individual transmission rods of the whole-body coil 5 are given. In addition, it must be ensured that at the appropriate time the magnetic resonance signals at the local coils 6 through the RF receiver unit 13 or possible signals on the whole-body coil 5 through the RF transceiver 12 be read out and processed further. The measuring control unit 15 gives the corresponding signals, in particular the multi-channel pulse train b to the high-frequency transmitting / receiving unit 12 and the gradient pulse train GP to the gradient controller 11 in response to a drive sequence specified in a control protocol P. In this control protocol P, all control data are stored, which must be set during a measurement.

Usually in a memory 16 a plurality of control protocols P for various measurements deposited. These could be over the terminal 20 be selected by the operator and optionally varied in order then to have a suitable control protocol P for the currently desired measurement, with which the measurement control unit 15 can work. Incidentally, the operator can also use a network NW control protocols P, for example from a manufacturer of the magnetic resonance system 1 , and then modify and use them if necessary.

However, the basic sequence of such a magnetic resonance measurement and the components mentioned for triggering are known to the person skilled in the art, so that they will not be discussed further here in detail. Incidentally, such a magnetic resonance scanner 2 and the associated control device 10 still have a variety of other components, which are also not explained in detail here.

It is noted at this point that the magnetic resonance scanner 2 may also be constructed differently, for example, with a laterally open patient space, and that in principle the antenna array used for transmission does not have to be constructed as a birdcage antenna. It is only essential that it has several separately controllable transmission channels S ₁ ,..., S _N , in the simplest case two transmission channels.

The measuring control unit 15 the control device 2 Here, for example, in the form of software modules has a reference pulse generation module 18 which initially generates a reference pulse train b _R according to the specifications in the control protocol P, which is to be played in a suitable manner with respect to the gradient pulses. This reference pulse train b _R is first to an RF pulse adjustment device 19 which also here as a software module within the measuring control unit 15 can be built. This RF pulse adjustment device 19 serves in the manner according to the invention in an HF pulse adjustment method or B ₁ shimming method for each of the radio-frequency transmission channels S ₁ ,..., S _N an individual complex transmission scaling factor SF ₁ ,. SF _N to determine. The RF pulse adjustment device has a candidate image generation unit 21 on, with the magnetic resonance system 1 is controlled such that a recording of a plurality of candidate images KB of an object to be examined O with different the candidate images KB associated Sendeskalierungsfaktoren SF ₁ , ..., SF _N takes place. The HF pulse adjustment device 19 also has a memory unit 22 for storing the recorded candidate images KB and the transmission scaling factors SF ₁ ,..., SF _N assigned to the respective candidate images. The storage unit 22 may be part of the memory, for example 16 be. The storage unit 22 but also in the measuring control unit 15 or integrated as a memory section in another unit in which a memory device already exists or can be integrated. Furthermore, the RF pulse adjustment device comprises 19 an analysis unit 23 for analyzing the recorded candidate images KB. As already described, the analysis with regard to various criteria can be carried out with different evaluation methods. The HF pulse adjustment device 19 also has a selection unit 24 for selecting optimal transmission scaling factors SF ₁ , ..., SF _N based on the analysis of the recorded candidate images KB with respect to a given criterion. The determined transmission scaling factors SF ₁ ,..., SF _N are finally multiplied by the reference pulse train b _R.

The final step of such a B ₁ shimming process is again schematically in FIG 2 shown. As can be seen here, the reference pulse train b _{R is} the one to the adjustment device 19 passed, which - as later with reference to 3 is explained - the complex Sendeskalierungsfaktoren SF ₁ , SF ₂ , SF ₃ ..., SF _N determined. These are, as shown schematically, multiplied by the reference pulse train b _{R in} order to obtain the individual pulse trains b ₁ , b ₂ , b ₃ ,..., B _N , which then together form the multi-channel pulse train b, which is via the high frequency send / receive unit 12 is sent out.

Alternatively, the RF pulse adjustment device 19 for example, also separately from the measuring control unit 15 built or part of the high-frequency transmitting / receiving unit 12 be, so that, for example, the multiplication with the complex Sendeskalierungsfaktoren SF ₁ , SF ₂ , SF ₃ ..., SF _N hardware is done. Likewise, the reference pulse generation module 18 a separate device or, for example, part of the high-frequency transmitting / receiving unit 12 be. The reconstruction unit 14 can also be the analysis unit 23 and / or the selection unit 24 exhibit.

As in the flowchart of 3 can be seen in the inventive method according to a preferred embodiment, first in the step 3.I a plurality of candidate images KB of an object to be examined having different candidate sets of transmission scaling factors SF ₁ , ..., SF _N recorded. Subsequently, at the step 3.II With regard to a given criterion, optimal transmission scaling factors SF ₁ ,..., SF _{N are determined} for each of the radio-frequency transmission channels S ₁ ,..., S _N on the basis of the recorded candidate images KB.

The extraction methods described in the literature (see above), also called B1-mapping, already provide the quantitative B1 distributions of each candidate image (as described in the references referred to above). Depending on the specific problem, it may be indicated e.g. Criteria for B1 homogeneity (particularly obvious and characterized by, for example, standard deviation of B1 values) or else thresholds for minimum and maximum B1 values, respectively.

4 also shows a flowchart of a method according to an embodiment of the invention. The step 4.I in 4 corresponds to the step 3.I in 3 , At the step 4.II the recorded candidate pictures (KB) are analyzed. Subsequently, at the step 4.III an optimal candidate picture KB selected and at the step 4.IV For example, the optimum transmission scaling factors SF ₁ , ..., SF _{N are determined} on the basis of the information obtained by analyzing the captured candidate images.

5 also shows a flowchart of a method according to an embodiment of the invention. The step 5.I in 5 corresponds to the steps 3.I respectively. 4.I in the 3 respectively. 4 , However, in the step of analyzing the captured candidate images KB, the method becomes 500 a particularly simple procedure chosen. It will be at the step 5.II taken candidate images KB in a display unit 20 displayed, then a selection of one of the candidate images is made, for example, by a person. After that, at the step 5.III receive a selection signal from a signal receiving unit. Finally, at the step 5.IV determines the optimum transmit scaling factors SF ₁ , ..., SF _N on the basis of the information received with the selection signal. The signal receiving unit can, for. B. a keyboard of a computer, such as the terminal 17 be.

These examples show how an adjustment of the B ₁ field can be carried out considerably faster and easier by the method according to the invention.

Finally, it is pointed out once again that the detailed methods and structures described above are exemplary embodiments and that the basic principle can also be varied within a wide range by those skilled in the art, without departing from the scope of the invention, as far as it is specified by the claims is. For the sake of completeness, it is also pointed out that the use of indefinite articles does not exclude "a" or "one", that the characteristics in question can also be present multiple times. Likewise, the term "unit" or "module" does not exclude that these consist of several components, which may possibly also be spatially distributed.

LIST OF REFERENCE NUMBERS

 1

Magnetic Resonance System / Magnetic Resonance System

 2

magnetic resonance scanner

 3

Basic field magnet

 4

gradient

 5

Whole body radio frequency coil

 6

local coil

 7

lounger

 8th

Examination room / patient tunnel

10

 control device

11

 Gradient controller

12

 High-frequency transmitter / receiver unit

13

 RF receiver unit

14

 reconstruction unit

15

 Measurement control unit

16

 Storage

17

 Terminal interface

18

 Reference pulse generating module

19

 RF pulse adjustment device

20

 terminal

21

 Candidate image generation unit

22

 storage unit

23

 analysis unit

24

 selector

 O

Object / patient / object of investigation

 P

control protocol

northwest

 network

BD

 image data

RD

 raw Data

GP

 Gradient pulse train

SG _x , SG _y , SG _z

 control signal

b

 Multichannel pulse train

b _R

 Referenzpulszug

b ₁ , ..., b _N

 pulse trains

S ₁ , ..., S _N

 transmission channel

SF ₁ , ..., SF _N

 Send scaling factor

m

 Target magnetization

JV, 100, 200, 300

 RF pulse adjustment method

QUOTES INCLUDE IN THE DESCRIPTION

This list of the documents listed by the applicant has been generated automatically and is included solely for the better information of the reader. The list is not part of the German patent or utility model application. The DPMA assumes no liability for any errors or omissions.

Cited non-patent literature

• W. Grissom et al .: "Spatial Domain Method for the Design of RF Pulses in Multicoil Parallel Excitation", Mag. Res. Med. 56, 620-629, 2006 [0011]
• "Chung, Kim, Breton and Axel: Rapid B1 + Mapping Using a Preconditioning RF Pulse with TurboFLASH Readout, Magnetic Resonance in Medicine 64: 439-446 (2010)" [0023]
• "Nehrke and Börnert: DREAM - A Novel Approach for Robust, Ultrafast, Multislice B1 Mapping, Magnetic Resonance in Medicine 68: 1517-1526 (2012))" [0023]

Claims (12)

RF Pulse Adjustment Method (JV, 300 . 400 . 500 ) for determining when driving a magnetic resonance system ( 1 ) with a plurality of radio-frequency transmission channels (S ₁ ,..., S _N ), over which HF pulse trains (b ₁ ,..., b _N ) are emitted in parallel during operation, transmit scaling factors (SF ₁ ,. SF _N ), wherein in the control for a plurality of the radio-frequency transmission channels (S ₁ , ..., S _N ) a common Referenzpulszug (b _R ) is predetermined, comprising the steps - recording a plurality of candidate images (KB) of one examining object (O) with different candidate sets of transmission scaling factors (SF ₁ , ..., SF _N ) ( 3.I . 4.I . 5.I ), Determining optimum transmission scaling factors (SF ₁ ,..., SF _N ) for each of the radio-frequency transmission channels (S ₁ ,..., S _N ) with respect to a given criterion on the basis of the recorded candidate images (KB) ( 3.II ). Procedure ( 400 ) according to claim 1, wherein the step of determining the optimal transmission scaling factors (SF ₁ , ..., SF _N ) comprises the following steps: - analyzing the recorded candidate images (KB) and - selecting an optimal candidate image (KB) ( 4.II ) and determining the optimal transmission scaling factors (SF ₁ , ..., SF _N ) on the basis of the information obtained by analyzing the recorded candidate images ( 4.III ). Method (JV) according to claim 2, wherein the transmission scaling factors (SF ₁ , ..., SF _N ) of the candidate set of transmission scaling factors (SF ₁ , ..., SF _N ) associated with the optimal candidate image are determined as optimal transmission scaling factors (SF ₁ , ..., SF _N ) are selected. The method of claim 3, wherein the selection of the optimal candidate image is based on a candidate image generated with a circularly polarized radio frequency magnetic field and a candidate image generated with an elliptically polarized magnetic field. Method (JV) according to one of claims 1 to 4, wherein the candidate images (KB) are overview images of the object (O). Method (JV) according to one of claims 1 to 5, wherein the candidate images (KB) show different regions and / or views of the object (O). Procedure (JV, 500 ) according to one of claims 1 to 6, wherein the analysis of the candidate images (KB) comprises the following steps: displaying the recorded candidate images (KB) in a display unit ( 5.II ), - receiving a selection signal in a signal receiving unit ( 5.III ). Method (JV) according to one of claims 1 to 7, wherein the selection of the optimal candidate image (KB) based on an automatic analysis of the recorded candidate images (KB) takes place. Method for controlling a magnetic resonance system ( 1 ) with a plurality of radio-frequency transmission channels (S ₁ , ..., S _N ) over which HF pulse trains (b ₁ ,..., b _N ) are emitted in parallel, wherein for several of the radio-frequency transmission channels (S ₁ , ..., S _N ) a common Referenzpulszug (b _R ) is given and for each of the high-frequency transmission channels (S ₁ , ..., S _N ) a Sendeskalierungsfaktor (SF ₁ , ..., SF _N ) is determined to calculate the RF pulse trains (b ₁ , ..., b _N ) for the transmission channels (S ₁ , ..., S _N ) on the basis of the reference pulse train (b _R ), wherein the HF pulse adjustment Method (JV) according to one of claims 1 to 7 for determining the optimal transmission scaling factors (SF ₁ , ..., SF _N ) is applied. RF pulse adjustment device ( 19 ) for a magnetic resonance system ( 1 ), which has a plurality of radio-frequency transmission channels (S ₁ ,..., S _N ), wherein the HF-pulse-adjustment device ( 19 ) is designed to provide for each of the high-frequency transmission channels (S ₁ , ..., S _N ) in each case an optimal transmission scaling factor (SF ₁ , ..., SF _N ) for one of the high-frequency transmission channels (S ₁ , .. ., S _N ) together to determine predetermined reference pulse train (b _R ), characterized in that the HF pulse adjustment device ( 19 ) - a candidate image generation unit ( 21 ), which is designed to receive the magnetic resonance system ( 1 ) in such a way that a recording of a plurality of candidate images (KB) of an object to be examined is carried out with different transmission scale factors (SF ₁ ,..., SF _N ) assigned to the candidate images (KB), - a memory unit ( 22 ) for storing the recorded candidate images (KB) and the transmission scaling factors (SF ₁ , ..., SF _N ) assigned to the respective candidate images, - an analysis unit ( 23 ) for analyzing the recorded candidate images (KB) and - a selection unit ( 24 ) for selecting, with respect to a given criterion, optimal transmission scaling factors (SF ₁ , ..., SF _N ) based on the analysis of the captured candidate images (KB). Magnetic Resonance System ( 1 ) with - a plurality of radio-frequency transmission channels (S ₁ , ..., S _N ), - a control device ( 10 ) which is designed to emit in parallel RF pulse trains (b ₁ ,..., b _N ) for carrying out a desired measurement via the radio-frequency transmission channels (S ₁ ,..., S _N ), and Pulse adjustment device ( 19 ) according to claim 9, which is adapted to supply the determined optimal transmission scaling factors (SF ₁ , ..., SF _N ) to the control device ( 10 ). Computer program, which is stored directly in a memory of an HF pulse adjustment device ( 19 ) of a magnetic resonance system ( 11 ) with program code sections in order to carry out all the steps of a method according to one of Claims 1 to 8, when the program in the HF pulse adjustment device ( 19 ) is performed.

Images